Apparatus for ultrasound medical treatment

Abstract: An ultrasound medical treatment system capable of determining the hot spot at high spatial resolution, and preventing the displacement of the hot spot from the focal point (7). In the system, the imaging device for obtaining image data of a treatment portion containing a treatment target (8) and an energy irradiation device (2) for applying an energy irradiation onto the treatment target (8) are controlled in such a manner that the imaging device is controlled to obtain hot spot detection image data after the energy irradiation device is controlled to apply an energy irradiation at a prescribed level, so that a hot spot indicating a change due to a temperature change caused by the energy irradiation at the prescribed level can be detected from the hot spot detection image data, The energy irradiation device is then controlled to apply a treatment energy irradiation at a treatment level higher than the prescribed level according to the detected hot spot.

Description: BACKGROUND OF THE INVENTION Field of the Invention The present invention relates to a medical ultrasound treatment apparatus for treating target by irradiating intense focused ultrasound from outside of a patient, and an ultrasonic medical treatment apparatus utilizing imaging device. An apparatus of this kind is known, e.g., from EP 0 170 416. Description of the Background Art The conventional non-invasive temperature measurement for the interior of the patient using the temperature dependent magnetic resonance (MR) parameters used in conjunction with the ultrasound medical treatment requires the complete data concerning the positional relationship of the organs and the temperature coefficients for the organs. Moreover, when the precision with respect to the temperature is to be improved, in order to improve the S/N ratio, the spatial resolution must be sacrificed. Thus, it has been inappropriate for the hyperthermia which requires high spatial and temperature resolutions. Also, when the temperature change occurs in the measurement target, the measured MR parameters are going to be changed because of its own temperature dependency, so that the change of the image due to the degeneration can be obscured, and the accurate judgement of the treatment effect cannot be made, such that the treatment is ended prematurely or applied excessively, and the efficiency of the treatment is lowered and the normal tissues can be affected. On the other hand, at the portion with significant motion such as the respiratory motion or heart beat motion, there has been a danger for the focal point of the irradiated energy to be displaced and to damage the normal tissues. Moreover, in a case of treating the relatively large treatment target such as a cancer by a very small focal point in a manner of scanning, the scanning plan (treatment plan) can be spoiled, and the overlooking of the energy irradiation position may occur. Furthermore, as known from EP 0 170 416, when the ultrasound imaging device is incorporated, the real time continuous monitoring of the treatment becomes possible, but the ultrasound imaging device can only provide 2D tomographic image, so that anything off the tomographic plane cannot be handled. Moreover, the ultrasound imaging device has low resolution so that the high precision setting of the focal point is difficult and it has been very difficult to trace the narrow region accurately. Now, in the ultrasound medical treatment apparatus, it is important to irradiate the intense ultrasound only to the treatment target and not to affect the normal tissues. However, when the tissues having different acoustic impedances are present on the irradiation route of the ultrasound, the refraction and reflection can be caused and the focal point is displaced. Also, when the object with considerably different acoustic impedance such as bone, lung, and clearance (intestinal gas) are present, the further propagation of the ultrasound can be prevented there, and the heat generation due to the absorption of the energy occurs at such a position, to cause the degeneration at an unexpected portion. Also, the tumor contains more numerous blood vessels than the normal tissues, and when the intense energy is irradiated, the blood vessel can be damaged and severe loss of blood can be caused. Moreover, the change of the acoustic characteristics of the thermally degenerated tissues has not been taken into account conventionally. In addition, during the intense ultrasound irradiation for treatment, there has been cases in which the patient abruptly moves by sensing the intense pain or heat, or some other reason, and in such a case the focal point of the intense ultrasound is displaced from the intended position so that there is a danger of damaging the normal tissues. On the other hand, in the ultrasound medical treatment, there is a need to monitor the treatment region and the ultrasound transducer, and ultrasound imaging is suitable for this purpose as it can provide the real time monitoring. However, the ultrasound imaging can be affected by the noises due to the ultrasound irradiation of the ultrasound medical treatment so that the monitoring during the treatment cannot be made. Even when the intermittent ultrasound irradiation is adopted to cope with this problem, the real time feature cannot be realized and the accurate ultrasound irradiation has been difficult due to the body movement and the respiratory motion. SUMMARY OF THE INVENTION It is therefore an object of the present invention to provide an apparatus for medical treatment capable of determining the hot spot at high spatial resolution, and preventing the displacement of the hot spot from the focal point. According to the present invention, this object is solved by a treatment apparatus as defined in claims 1 and 8. Other features and advantages of the present invention will become apparent from the following description taken in conjunction with the accompanying drawings. BRIEF DESCRIPTION OF THE DRAWINGS Fig. 1 is a schematic block diagram of a first embodiment of an ultrasound medical treatment apparatus according to the present invention. Fig. 2 is a perspective view of a phased array type ultrasound transducer used in the apparatus of Fig. 1. Figs. 3A and 3B are 2D and 3D images obtained in the apparatus of Fig. 1 before and after the ultrasound irradiation, respectively. Fig. 4 is a flow chart for one operation of the apparatus of Fig. 1. Fig. 5 is a flow chart for alternative operation of the apparatus of Fig. 1. Fig. 6 is a schematic block diagram of a modified configuration for the apparatus of Fig. 1. Fig. 7 is sequential illustrations of images used in the apparatus of Fig. 6 in obtaining a hot spot image. Fig. 8 is an illustration of an exemplary display used by the apparatus of Fig. 6 for indicating a dangerous region. Fig. 9 is a timing chart for explaining an operation of a second embodiment of an ultrasound medical treatment apparatus according to the present invention. Fig. 10 is an illustration of a treatment target for explaining an operation in the second embodiment. Fig. 11 is a timing chart for explaining an operation of the second embodiment. Fig. 12 is a graph of image data used in the second embodiment for explaining another operation in the second embodiment. Fig. 13 is a timing chart for explaining another operation in the second embodiment. Fig. 14 is another timing chart for explaining still another operation in the second embodiment. Fig. 15 is a schematic block diagram of a third embodiment of an ultrasound medical treatment apparatus according to the present invention. Figs. 16A and 16B are illustrations of mesh shaped tag that can be used in the apparatus of Fig. 15. Fig. 17 is an illustration of a treatment region used in the apparatus of Fig. 17. Fig. 18 is a schematic block diagram of a fourth embodiment of an ultrasound medical treatment apparatus according to the present invention. Figs. 19A and 19B are timing charts for explaining an operation in the fourth embodiment. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS Referring now to Fig. 1, the first embodiment of an ultrasound medical treatment apparatus according to the present invention will be described in detail. The ultrasound medical treatment apparatus of this first embodiment is of a type which incorporates the nuclear magnetic resonance imaging (MRI) apparatus, and has a configuration as shown in Fig. 1. First, an ultrasound treatment part in this configuration of Fig. 1 will be described. Namely, the ultrasound treatment part includes an ultrasound applicator 1 which comprises an ultrasound transducer 2 for irradiating intense ultrasound for treatment, and a water bag 5 for containing a coupling fluid 4 for leading the intense ultrasound from the ultrasound transducer 2 to a patient 3. Here, the ultrasound transducer 2 has a circular disk shaped phased array structure which is divided in radial and circumferential directions as shown in Fig. 2. This ultrasound transducer is connected with driving circuits 12 which drive the ultrasound transducer 2 to irradiate the intense ultrasound at a time of the treatment in order to treat the treatment target located at a focal point 7 by heating the treatment target such as a tumor 8 at a high temperature. In this first embodiment, as the phased array type ultrasound transducer 2 is employed, it is possible to control the driving timings of the driving circuits 12 by phase control circuits 11, such that the focal point position, the acoustic field, and the heated region can be controlled without moving the applicator 1. Here, the driving circuits 12 are divided into a number of channels corresponding to the divided sections of the ultrasound transducer 2, and each channel can be driven independently by independent timing signals obtained at the phase control circuits 11 by applying delays to the control signals from a system controller 9. In this manner, the focal point of the ultrasound generated by the ultrasound transducer 2 can be set at any desired 3D position, as indicated by points 7 and 7' shown in Fig. 2 for example. The ultrasound applicator 1 is movably supported by a mechanical arm 17 which is controlled by the system controller 9 though an applicator position detection unit 15. The system controller 9 has functions of a controller for the ultrasound treatment part as well as a sequence controller and a data processing unit for an MRI part to be described below. Next, the patient positioning part and the MRI part in the configuration of Fig. 1 will be described. The patient 3 is placed on a treatment table 22, and carried into an MRI gantry 23 in which a magnet 18, gradient coils 19, and an RF coil 20 for MR imaging are provided, by a table drive device 21 controlled by the system controller 9. Here, in order to prevent the disturbance of the magnetic fields used in the MRI due to the ultrasound applicator 1, there is a need to form the ultrasound applicator 1 by non-magnetic materials as much as possible. For example, the ultrasound applicator 1 and the mechanical arm 17 can be made of materials such as reinforced plastic and austenitic cast iron which has nearly the same mechanical property as the usual cast iron while being non-magnetic. It is also possible to make the mechanical arm 17 to be a hydraulic type rather than an electrical type using an electric motor, to further reduce the amount of magnetic material. Next, the system controller 9 activates a gradient field power source 13 and a transmitter and receiver circuit 14 according to a prescribed pulse sequence such as that of the T2 weighted imaging scheme which is commanded from a console 16, so as to obtain the 3D MR image data for an interior of the patient 3, which are subsequently stored in a memory (not shown). Here, according to the MR images of the interior of the patient 3 obtained by the MRI part, it is possible to set up an appropriate treatment plan in advance. When the MR images are obtained, the system controller 9 controls the mechanical arm 17 to attach the ultrasound applicator 1 on the patient 3. Here, the position of the focal point 7 of the ultrasound to be irradiated from the ultrasound applicator 1 can be calculated and memorized by the system controller 9 according to an applicator position detected by the applicator position detection unit 15 containing potentiometers (not shown) attached on various parts of the mechanical arm 17, and the data on an attachment position of the mechanical arm 17 with respect to the MRI part measured in advance, such that the position of the focal point 7 can be indicated on the MR images displayed by a CRT 10 as shown in Fig. 3A. Also, in addition to the focal point 7, the ultrasound incident route 24 can also be indicated on the MR images displayed by the CRT 10 as shown in Fig. 3A. Moreover, as shown in Figs. 3A and 3B, the x, y coordinates in a case of 2D display or the x, y, z coordinates in a case of 3D display can also be indicated on the MR images displayed by the CRT 10 so as to indicate the positional relationship of the focal point 7 and the tumor 8. Now, in this ultrasound medical treatment apparatus of Fig. 1, a measurement of a hot spot caused by the irradiation of the ultrasound can be utilized in the treatment procedure as follows. Namely, the hot spot measurement can be utilized in confirming the coincidence of the treatment target and the treatment position by generating the hot spot before the actual treatment and measuring the position of the hot spot. Here, however, the generated hot spot may be located on a normal tissue, so that the ultrasound irradiation condition such as the ultrasound power to be used in generating the hot spot should be carefully controlled so as not to cause any damage to the tissues. In this regard, in the field of the hyperthermia, the relationship of the heating temperature and time with respect to the treatment effect (survival rate) for a cell has been established as expressed by the following equation (1): where T ⊘ is the temperature before the energy irradiation, ΔT(t) is a time profile of the temperature change, Ea is an empirical activation energy, A is a proportional constant, R is a gas constant, and S is the survival rate for a cell after the heating. Here, the empirical activation energy Ea can be related to the enthalpy Δ H of the degeneration according to the following equation (2): Ea = Δ H + R × T so that this empirical activation energy Ea can be obtained from the enthalpy of the degeneration reaction characteristic to the target cell. Alternatively, the activation energy Ea and the proportional constant A for the target cell can be measured by conducting the experiment using the target cell, as these quantities can be different for different types of the cell. From the past experiments, it is believed that the ranges for these quantities are approximately 50 Kcal/mol < Ea < 200 Kcal/mol and 10 90 < A < 10 780 . Thus, by setting the final survival rate S according to the above equation (1) at a sufficiently high level, and controlling the ultrasound irradiation to guarantee this setting level, the damage to the normal tissues due to the generation of the hot spot can be prevented effectively. For example, the setting of over 0.7 for the survival rate S should be sufficient in practice. Now, the procedure for the generation and the measurement of the hot spot as well as its use in the treatment according to this first embodiment will be described in detail. In this first embodiment, the measurement of a temperature change based on the T1 weighted images is employed. Before the treatment, the imaging for the positioning purpose is carried out, and the patient is positioned according to a displacement detected by comparing the image obtained by this imaging and the image obtained at a time of the treatment plan set up. After this positioning, the T1 weighted image is acquired as a reference image for the hot spot measurement to be carried out prior to the intense ultrasound irradiation. The obtained reference image is stored in a memory (not shown). Here, the imaging for the hot spot measurement purpose can be carried out in 2D or 3D. In a case of 2D imaging, the slice plane is set up to include the setting focal point thereon. Then, the system controller 9 controls the phase control circuits 11 and the driving circuits 12 to irradiate the ultrasound from the ultrasound transducer 2 while controlling the intensity and irradiation time to be in ranges of not causing the degeneration according to the above equation (1). On the other hand, under the control of the system controller 9, the T1 weighted image is imaged similarly as above, either continuously since a time prior to the ultrasound irradiation, or during the ultrasound irradiation such as after three seconds since the start of the ultrasound irradiation. Then, the difference between the obtained T1 weighted image and the reference image stored in the memory is calculated to obtain a hot spot image. Here, there is no need to calculate the difference in a case the tissues were uniform when the reference image was imaged, or in a case the temperature change sensitive imaging can be carried out by adjusting the pulse sequence appropriately such that the sufficient temperature change appears on the obtained T1 weighted image itself. It is also possible to calculate the changes of the signal values obtained by the pulse sequence in advance, and identify the hot spot as a portion at which the change exceeds the prescribed threshold. From this hot spot image, the peak point or a region with change exceeding the prescribed threshold is extracted as an image of the hot spot 6, which is superimposed onto the MR image of Fig. 3A obtained at the beginning, as shown in Fig. 3B. Then, a displacement of a peak point of the observed hot spot 6 from the original setting focal point 7 is detected. Here, in a case of the 2D imaging, the displacement of the peak point within the slice plane can be detected from one MR image, and the displacement in a direction perpendicular to the slice plane can be detected by carrying out another hot spot imaging on a plane perpendicular to the slice plane which passes through the detected peak point. Alternatively, when the difference between the temperature change at the peak point and the predicted temperature increase is below a prescribed threshold, it can be judged that the peak point of the hot spot 6 is not contained in the slice plane. Also, even in a case of the 2D imaging, when the multi-slice imaging is possible, a central slice plane is set up to contain the setting focal point such that the peak point on the central slice plane can be detected, and then the peak point in the slicing direction can be obtained from the change of the pixel representing the detected peak point among the slice planes. In a case the detected displacement exceeds a prescribed tolerable range, the danger is notified to an operator by a warning sound, a screen display of a warning color or text, etc., while a safety circuit (not shown) is activated to stop the irradiation of the intense ultrasound. Alternatively, the setting of the focal point 7 can be adjusted to place the hot spot at the original setting focal point, and then the measurement of the hot spot can be repeated. In this manner, when the hot spot coincides with the setting focal point position within a prescribed range, the irradiation level of the ultrasound is increased to the treatment level to heat up the treatment target at the hot spot over 80 °C for example, so as to thermally degenerate the treatment target to death. Thereafter, the position of the setting focal point 7 is moved to subsequent treatment targets sequentially and the similar operation as described above is repeated for each treatment target. In the above procedure, in a case the hot spot 6 cannot be generated when the ultrasound at a reduced power is irradiated, it is either a malfunction of the ultrasound generator or the ultrasound transducer, or a dislocation of the coupling, or else an abnormality such as an extreme refraction, de-focusing, etc. of the ultrasound. In either case, the system controller 9 controls the system to output the warning similar to that used in the above procedure. At an end or in a middle of the original treatment plan, the irradiation of the ultrasound is stopped and the progress of the treatment is observed by taking the MR image in a vicinity of the treatment portion and checking the change in the living body on the MR image in a manner similar to that described above. During this operation, the applicator 1 remains to be attached to the patient 3. At this point, by subtracting the data obtained here from the data of the T2 weighted image stored in the memory before the treatment began, it becomes possible to confirm the thermally degenerated region clearly, so that it becomes possible to judge whether sufficient treatment had been carried out or the re-treatment is necessary as the treatment was insufficient. This confirmation operation can be incorporated into the treatment table from the beginning, such that the necessary MR imaging takes place automatically at prescribed time intervals. When it becomes possible to judge that the sufficient treatment had been completed according to the treatment effect check using the MRI, the operator terminates the treatment. At this point, the system controller can call up the record of the treatment conditions from the memory, and output the treatment record from the CRT 10. The above described operation according to this first embodiment can be summarized as shown in the flow charts of Figs. 4 and 5, where Fig. 4 concerns with a procedure for measuring the hot spot from the difference with respect to the reference image, while Fig. 5 concerns with a procedure for measuring the hot spot as that which is smaller than the predicted image signal change due to the temperature. Namely, the operation according to the flow chart of Fig. 4 proceeds as follows. First, the 3D fine imaging of the patient is carried out at the step 50, and the treatment plan is set up according to the obtained 3D MR image at the step 51. Here, N focal points of the ultrasound to be used in the treatment are set up. This completes the treatment plan stage. Next, in the treatment stage, the patient is placed inside the MRI gantry at the step 52, and the 3D imaging of the patient is carried out at the step 53. Then, the displacement between the 3D MR image obtained at the step 53 and the 3D MR image used at the step 51 in setting up the treatment plan is detected at the step 54. In a case the detected displacement is greater than a prescribed threshold Q1 at the step 55, the patient is moved as much as the detected displacement at the step 56, whereas otherwise this step 56 is skipped. Then, a counter i is set to 0 initially at the step 57, and this counter is incremented by one at the step 58. If the counter i is greater than the number N of setting focal points at the step 59, the imaging for the treatment effect check is carried out at the step 60, and whether the sufficient treatment had been carried out or not is judged at the step 61. If so, the treatment operation is terminated, whereas otherwise the operation returns to the step 50 to repeat the treatment again. When the counter i is not greater than N, the i-th focal point is set up at the step 62. Then, the reference image is taken at the step 63 and stored in the memory at the step 64. Meanwhile, the weak ultrasound is irradiated onto the patient at the step 65, and the MR image under the weak ultrasound irradiation is obtained at the step 66. Next, the difference between the MR image obtained at the step 66 and the reference image obtained at the step 63 as stored at the step 64 is obtained at the step 67, and the hot spot peak is detected from the obtained difference at the step 68, and then the displacement of the detected hot spot peak from the setting focal point is detected at the step 69. When the detected displacement is greater than a prescribed threshold Q2 at the step 70, the setting focal point is moved as much as the detected displacement at the step 71 and the operation returns to the step 65, whereas otherwise the high intensity ultrasound is irradiated onto the patient to carry out the treatment at the step 72. and then the operation returns to the step 58 to repeat the similar operation for the next setting focal point. On the other hand, the operation according to the flow chart of Fig. 5 proceeds as follows. Here, those steps which are substantially equivalent to those in the flow chart of Fig. 4 are given the same reference numerals in the figure and will not be described in detail again. In this case, the steps 50 to 62 are identical to those in the flow chart of Fig. 4. After the step 62, the operation directly proceeds to the steps 65 and 66 which are also identical to those in the flow chart of Fig. 4. Next, after the step 66, a region in the MR image obtained at the step 66 which is exceeding a threshold given by the image signal is extracted at the step 73, and a peak within the extracted region is detected at the step 74. Then, the operation proceeds to the steps 69 to 72 which are also identical to those in the flow chart of Fig. 4. It is to be noted that, in the first embodiment described above, a body cavity coil to be inserted within the patient may be used instead of the RF coil 20. In addition, the phased array type ultrasound transducer 2 may be replaced by the annular array type ultrasound transducer, and the focal point may be moved by mechanically controlling the applicator 1. Now, various modifications of the first embodiment of a medical treatment apparatus according to the present invention will be described in detail. First, the ultrasound medical treatment apparatus of the first embodiment of Fig. 1 can be modified to further incorporate the ultrasound imaging device as shown in Fig. 6. Here, those elements which are equivalent to the corresponding elements in the first embodiment will be given the same reference numerals in the figure and their descriptions will be omitted. In this case, an ultrasound probe 25 is attached at a center of the ultrasound transducer 2 and connected with a ultrasound imaging device 26 controlled from the system controller 9 such that the ultrasound tomographic image of the interior of the patient 3 can be observed in real time. This ultrasound probe 25 is formed to be slidable back and forth as well as rotatable around its axis. By providing means for obtaining the relative position of the ultrasound probe 25 and the focal point 7 of the ultrasound generated from the ultrasound transducer 2, it is possible to indicate the focal point position on the ultrasound tomographic image obtained by the ultrasound imaging device 26. It is also possible to indicate the position of the ultrasound tomographic image on the 2D or 3D MR image obtained by the MRI part, so as to utilize the ultrasound tomographic image along the treatment plan set up in accordance with the MR image. Here, it is to be noted that the applicator 1 is not necessarily limited to be used as an upper side approaching type as shown in Fig. 6, and can be used as a lower side approaching type by controlling the mechanical arm 17 appropriately. Now, with regard to the hot spot 6, if suffices to determine a region with a relatively high temperature, so that there is no need to indicate the temperature change quantitatively, and it is only required that the hot spot 6 be clearly identifiable in the image reflecting the temperature change. For example, in the T1 weighted image obtained by the MRI, it is difficult to indicate the relaxation time T1 quantitatively by just one such image, but it exhibits a sufficient change in proportion to the temperature so that a single T1 weighted image can be used for the purpose of the hot spot measurement. In this case, the intensity and irradiation time for the ultrasound irradiation are set up to be in ranges of not causing the degeneration to obtain the temperature profile satisfying the above equation (1). For example, the relationships among the intensity, irradiation time, and the temperature profile are obtained experimentally in advance and stored in a memory (not shown), and the survival rate according to the temperature profile is calculated by using the above equation (1), to confirm that the resulting survival rate is within a setting range before the irradiation. Alternatively, there are experimental results indicating that, in a case of an instantaneous heating (one second or shorter), the product of the ultrasound focal point intensity, irradiation time, and frequency is going to be proportional to the temperature change as can be expressed by the following equation (2): I p × t × f = 50ΔT where I p is the focal point intensity, t is the irradiation time, and f is the frequency, so that the temperature increase ΔT can be calculated from this equation (2). The actual temperature is expected to be lower than the calculated temperature, and will decrease exponentially with a certain time constant after the irradiation. This time constant depends on the type of the tissue, and can be determined in advance experimentally. Thus, when the temperature profile predicted in this manner is substituted into the above equation (1), if the survival rate is within the setting range, the degeneration is not going to occur. In a case of the irradiation time over one second, the proportional relationship of the above equation (2) does not hold, but within the range in which the influence of the blood flow is ignorable, the living body heat transport equation can be solved to obtain the distribution of the heat sources, and it is possible to calculate the temperature profile which is in agreement with the experimental results for the irradiation time below twenty seconds. Instead of obtaining the temperature profile from the calculations as described above, it is also possible to obtain the quantitative temperature change distribution intermittently by utilizing the above described temperature distribution measurement technique such as the temperature measurement using the water proton chemical shift, and the obtained result can be substituted into the above equation (1) to calculate the survival rate distribution every time the image is obtained. Then, the irradiation conditions can be controlled such that the irradiation power is decreased or the irradiation time is shortened when the survival rate becomes lower than the setting range. In the above, it has been assumed that the focal point and the peak point of the hot spot are coinciding, but it has been experimentally confirmed that there is a tendency for the hot spot to be displaced toward the ultrasound irradiating side due to the influences of the dissipation within the living body, etc. Also, in a case of causing the degeneration in a region irradiated by the intense ultrasound, due to the degeneration and the cavitation caused at an early stage of the irradiation, the ultrasound is not going to reach beyond them, and it has been experimentally observed that the degenerated region tends to spread toward the ultrasound irradiating side. According to such an observation, it is possible to experimentally determine a region at which the degeneration can be caused when heating is applied at certain irradiation conditions, and after the positional relationship of this region with respect to the focal point and the hot spot is comprehended, the treatment region can be set up to be aligned with the predicted degeneration region, such that the degeneration region can be predicted from the measured hot spot. Also, instead of making the temperature change measurement using the T1 weighted image, it is also possible to use any temperature dependent parameter that can be observed to sense the temperature change according to the change of the observed parameter. For example, any of the above mentioned parameters of the MRI can be utilized. In a case of the temperature measurement utilizing the temperature change obtained by the water proton chemical shift, it is possible to determine the change due to the temperature change quantitatively, so that the temperature change can also be determined quantitatively. The same applied also to the other imaging diagnostic apparatus such as X-ray CT and ultrasound imaging devices. For example, the temperature dependence of the sonic speed of the ultrasound can be utilized to extract the change due to the temperature change as an image. In order to extract the image change due to the temperature, it is going to be necessary to take a difference between the images before and after the heating, pixel by pixel. However, when the patient moves during the heating, the obtained difference will be that between non-corresponding pixels, and the large error can be caused especially at the tissue boundaries. Such a body movement of the patient can be compensated as follows. Namely, the heated region within one image is limited in a vicinity of the focal point, so that the image data outside of the region in a vicinity of the focal point can be considered as not receiving the influence of the heating. Consequently, as shown in Fig. 7, the pattern matching of the images before and after the heating shown in (a) and (b) of Fig. 7 can be made according to the image data outside of the shaded region set up in vicinity of the focal point, so as to detect the displacement between these images. Then, these images can be aligned according to the detected displacement as shown in (c) of Fig. 7, and the difference can be taken in this aligned state, to obtain the hot spot 6 without the influence of the body movement as shown in (d) of Fig. 7. Also, instead of using the image obtained before the ultrasound irradiation as the reference image as described above, it is possible to use the previously taken image as the reference image and to obtain the temperature change from the integrated change in the difference image of the previously taken image and the presently taken image, so as to reduce the influence of the body movement. By applying the pattern matching from time to time to compensate the body movement in such a manner, it becomes possible to follow the large body movement. In particular, when the chemical shift temperature measurement is employed, as the temperature resolution can be set up arbitrarily in a case of measurement using the phase mapping, it becomes possible to make the measurement of the temperature distribution at the fine temperature resolution over a wide range, by obtaining the temperature distribution as the integration of results obtained by setting the measurement temperature width in a narrow range which can only satisfy the temperature change between one imaging interval. It is to be noted that the idea of the survival rate according to the above equation (1) can also be utilized in the evaluation of the safety during the entire treatment as follows. Namely, by constantly obtaining the temperature distribution over the wide range including the irradiation route and focal point, the survival rate at each pixel can be calculated according to the past temperature profile. Then, by setting the threshold for the dangerous survival rate in advance, the occurrence of the portion reaching to this threshold can be noticed to the operator by displaying a colored region 27 as shown in Fig. 8 as the dangerous survival rate region, or by means of an alarm sound, while the irradiation is stopped or shifted away from that portion to cool down that dangerous portion. In this manner, it is possible to prevent the hyperthermia type influence from being applied to the normal tissues. At this point, the calculation range can be limited to the particularly interested point such as the body surface, or a portion at which the reflection from the intestinal wall can be expected. Also, instead of calculating the survival rate according to the above equation (1), it is also possible to set up the threshold for the temperature itself, such that the warning to the operator similar to that described above is given when the temperature reaches to this threshold, while the irradiation is stopped or shifted away from that portion to cool down that dangerous portion. In addition, the temperature measurement can be utilized not just in a case of using the irradiation energy level below the treatment level as in the hot spot measurement but also in a case of using the irradiation energy level at the treatment level for the purpose of checking the resulting heating. In such a case, however, the measured parameter can be changed due to the degeneration of the treatment target, and this change is expected to be superposed on the actual temperature change. For this reason, the image can be obtained in the degenerated state in advance, and the change due to the degeneration can be subtracted from the image obtained during the heating so as to reduce the influence due to the degeneration. Alternatively, the correspondence between the image change and the temperature can be obtained in advance for regions including the region to be degenerated, and the temperature distribution can be obtained by the calculation according to this correspondence. It is to be noted that the schemes described above are equally applicable to the thermal medical treatment other than the ultrasound medical treatment described here. For example, in the heating treatment using the laser, it is also possible to check the heating region by measuring the hot spot while heating at conditions for not causing the degeneration which are determined in advance. Similarly, the heating region can be checked in the heating treatment using the microwave. Next, the second embodiment of a medical treatment apparatus according to the present invention will be described in detail. In this second embodiment, the configuration of the apparatus is essentially similar to that of the first embodiment described above, so that its description will not be repeated here. In this second embodiment, in order to obtain the image of the degeneration, the image is taken after the temperature of the heated portion has returned to the normal temperature. Namely, as indicated in Fig. 9, by taking the interval between the irradiation period P1 and the imaging period P2 over a prescribed length of time determined by the heating conditions such as the irradiation energy and the irradiation time, the temperature can return to the normal temperature and the change on the image can be limited to the irreversible change due to the degeneration alone. According to the animal experiment done by Vallancien et al. (Eur. Urol. 1991; 20; 211-219), the pig's liver heated up to 108 °C by the ultrasound irradiation of 0.25 second returns to the normal temperature within about eight seconds. Thus, by setting the imaging period P2 at a shaded region in Fig. 9 which starts after the sufficient amount of time such as eight seconds for example from the irradiation period P1, it becomes possible to obtain the image resulting from the change S1 in the NMR signals due to the degeneration alone. Here, however, in the living body, there is a possibility for the edema to appear as the living body reaction after several tens of minutes since the heating treatment, and this edema can make it difficult to take the image of the degeneration, so that in order to obtain the image of the degeneration as purely as possible, the imaging should be carried out after the temperature has returned to the normal temperature, and before the edema appears. In a case of carrying out the treatment intermittently by sequentially shifting the treatment position over a large tumor, it is timewise inefficient to take the image after each ultrasound irradiation, so that the ultrasound treatment can be carried out while obtaining the MR images sequentially at intervals of several tens of ms by using the ultra high speed pulse sequence and checking the treatment effect (degeneration) on the portion which has returned to the normal temperature within the obtained MR images. For example, in a case of treating the treatment target (tumor) 8 as shown in Fig. 10, the ultrasound treatment can be carried out at the treatment portions shifted in an order indicated by the encircled numbers as shown in Fig. 10. In such a case, the treatment positions can have the temperature characteristics as indicated in Fig. 11. According to this Fig. 11, the temperature of the first treatment position has returned to the normal temperature by the time the eighth treatment position is to be treated, so that the treatment effect on the first treatment position can be checked from the MR image taken at a period A indicated in Fig. 11. Also, by making the temperature measurement in real time by using the chemical shift temperature measurement, it becomes possible to check the treatment effect without the influence of the temperature from the MR image of the degeneration obtained when the temperature is known to have returned to the normal temperature. In operating this ultrasound medical treatment apparatus as a whole, the operator can operate the track ball and the mouse by both hands, such that the imaging slice plane is selected by the track ball operated by the left hand, while the selection and determination of the treatment position as well as the start of the ultrasound irradiation can be specified by the mouse operated by the right hand. In this manner, the 3D treatment target can be treated while checking the treatment effect. Here, it becomes possible to check the treatment effect easily by displaying the already treated portion after a prescribed period determined by the heating conditions in different color, while also changing displayed colors for the presence or absence of the degeneration as well as for different levels of the degeneration. The image data obtained by the imaging are stored in the memory and can be called up at a time of checking the treatment effect after the treatment is over. Here, it is possible to extract parts of the images containing the position to be treated by one ultrasound irradiation from the images, and synthesize the extracted parts for the purpose of checking the treatment effect. In a case of carrying out the treatment automatically according to the treatment plan set up in advance, it is possible to carry out the automatic treatment accurately while judging the treatment effect as follows. Namely, for each treatment at one focal point, the occurrence of the degeneration at the treatment portion in the image obtained after the prescribed period determined by the heating conditions is checked with respect to the threshold determined from the past experimental data, and then the feed back for commanding the re-treatment is returned to the system controller in a case the treatment is insufficient. In the imaging of the degeneration after the temperature has returned to the normal temperature as described above, the treatment effect immediately after the irradiation of the ultrasound cannot be judged. Also, in a case of heating a larger region over a certain period of time, a considerable amount of time is required until the temperature returns to the normal temperature, so that it is necessary to extract the degeneration alone in the high temperature state. In such a case, the degeneration can be judged as follows. Namely, by utilizing the characteristics of the image signal known from the experiences, the degeneration can be judged from the MR image obtained at the time of the temperature increase. For example, the various characteristics such as the temperature increase characteristic with respect to the irradiation time as shown in Fig. 9, the image signal strength characteristic with respect to the imaging sequence, and the threshold for causing the degeneration for the general heating conditions can be stored in the memory in advance, such that at a time of the ultrasound irradiation, the occurrence of the degeneration and the level of the degeneration can be monitored in terms of the measured image signal strength. Similarly, as shown in Fig. 12, by predicting the change S3 due to the temperature alone in the measured image data, the measured data containing the change S2 due to the degeneration can be corrected. Namely, the temperature distribution can be measured by using the temperature distribution measurement by the chemical shift in the procedure shown in Fig. 13, and the relaxation times measured at the high temperature can be corrected by the measured temperature distribution to obtain the change due to the degeneration alone as follows. First, at the point A, the image is obtained while the temperature distribution is measured before the heating treatment. Then, at the point B, the heating treatment is carried out by the ultrasound irradiation. During and after this heating treatment, at the points C and D, the image and the temperature distribution are also obtained. Then, the influence of the temperature is corrected according to the temperature dependency of the image (such as T2 weighted image). In this case, the temperature distribution measurement obtains the absolute temperature calculated from the displacement with respect to the fat spectrum, but in a case the influence of the magnetic field inhomogeneity is not large due to the degeneration, the temperature measurement utilizing the phase data can be used to obtain the relative temperature distribution with respect to the temperature distribution before the heating treatment, in order to reduce the measurement time. Also, without measuring the temperature distribution as described above, on an assumption that the temperature distribution at a certain amount of time after the ultrasound irradiation has a uniform shape with only amplitude changing with respect to the irradiation intensities, the correction can be made as follows. First, the ultrasound weak enough not to cause the degeneration is irradiated, while the MR images are obtained continuously. Then, at a time of the actual heating treatment, the image data are also obtained similarly. Then, the image obtained for the weak ultrasound is changed in proportion to the ultrasound irradiation energy to calculate the change of the image due to the influence of the temperature alone, and the change due to the degeneration alone can be extracted from the image obtained at a time of the heating treatment according to the calculated change due to the temperature. Also, after the ultrasound irradiation, the temperature distribution gradually spread spatially due to the influences of the distribution, etc. Thus, by applying the ultrasound intense enough to cause the degeneration, and the change of the image due to the temperature change for the region near the focal point at which the degeneration is caused is predicted by the fitting of the temperature distribution with respect to the temperature distribution known from experiences, or by the polynomial approximation of the temperature distribution, for the image data in a region slightly distanced from the focal point at which the temperature is changing but the degeneration is not caused. Then, the change due to the degeneration can be extracted by subtracting the predicted change due to the temperature change from the measured image. Here, the image data for the the qualitative image such as T1 weighted image and the T2 weighted image are used so that the extracted result concerning the presence or absence of the degeneration can also be displayed qualitatively by the simple subtraction at each picture element. In order to extract the level of the degeneration quantitatively, the influence due to the temperature change can be corrected as in the above by calculating the relaxation times such as T1 and T2 for each picture element by solving the simultaneous equations from a plurality of images with different repetition times and the echo times obtained by the ultra high speed sequence within a sufficiently short period in which the temperature change can be ignored. Alternatively, assuming that a sum of the inverse of the relaxation time due to the temperature change and the inverse of the relaxation time due to the degeneration is equal to the inverse of the actually measured relaxation time, the relaxation time due to the degeneration can be calculated from this relationship, and the quantitative image of the degeneration can be obtained. In the spin echo scheme, the signal strength S can be expressed in terms of the spin density A, the relaxation times T1 and T2, the repetition time TR, and the echo time TE, as in the following equation (3). S = A (1 - exp(TR × T1))exp(TE × T2) Then, for example, as shown in Fig. 14, at each of before, during, and after the treatment, a plurality (three in Fig. 14) of imagings (A1, A2, and A3; C1, C2, and C3; D1, D2, and D3) are carried out in such a manner that for the first and second imagings the echo time TE is fixed while the repetition time TR is changed, and the echo time TE is changed for the third imaging. Then, the echo signal for the first imaging is purely affected by the decaying term of T2 alone, so that by taking the ratio of the first and second image data and substituting it into the expression for it obtained from the above equation (3), it becomes possible to obtain T2. Then, after the third imaging, the obtained T2 is substituted into the above equation (3) and the simultaneous equations for the first and third image data can be solved for the spin density A and the relaxation time T2. In this manner, the relaxation times are calculated immediately after the imagings of each group (A, C, and D), to obtain the relaxation time images. Here, the calculation can be limited to a region in vicinity of the focal point at which the change can be expected. Meanwhile, the temperature measurement is also carried out for all the groups, and the temperature distribution is determined as the measured result as it is when the temperature change within each group is in an ignorable range, or as the average of the measured results. Then, using these temperature distribution data, the relaxation times measured during the temperature increase are corrected. When the temperature change within each group is large, the measure such as the shortening of the measurement interval is taken. The measurement interval (repetition time) and the echo time within each group are determined by the measurement target and the heating conditions. It is to be noted that the schemes described above are equally applicable to the heating treatment other than the ultrasound medical treatment described here. For example, they are applicable to the heating treatment using the laser guided by the optical fibers. In particular, the extraction of the degeneration during the temperature increase is applicable to the heating treatment using the microwave. Also, the change of the parameters such as the relaxation times due to the thermal degeneration has been utilized for the checking of the treatment effect above, but the change of the metabolism activity can be detected by using the spectroscopy for phosphorus in the hyperthermia in which the metabolism activity of cells are changed by the heating and the cells are eventually killed. For example, the change of the peak of ATP can be detected, and when its change is over the prescribed threshold, this information can be fed back as the treatment effect data as in the above, such that the treatment can be carried out while checking the treatment effect as in the above. Next, the third embodiment of a medical treatment apparatus according to the present invention will be described in detail. Here, those elements which are equivalent to the corresponding elements in the first embodiment of Fig. 1 will be given the same reference numerals as in the figure and their descriptions will be omitted. In this third embodiment, the ultrasound medical treatment apparatus of the first embodiment of Fig. 1 is slightly modified to further incorporate a chest belt 35 attached on the chest portion of the patient 3 for detecting the respiration waveform of the patient 3. Namely, in setting up the treatment plan for the treatment target such as the liver cancer at which the motion due to the respiration is considerable, it is preferable to use the image data obtained at the time phase near the expiration end in order to achieve the reproducibility of the images. For this reason, in this third embodiment, the chest belt 35 is provided to detect this time phase, such that the imaging timing can be controlled appropriately by the system controller 9 to which the detected respiration waveform signal is supplied from this chest belt 35. When the treatment started according to the treatment plan, at the inspiration end, the tagging is made at a predetermined treatment start position, and the focal point 7 of the ultrasound is set to the treatment start position and the intense ultrasound irradiation is started. Here, the tagging is the magnetic marking technique developed for the MRI (Zerhouni E.A., et al. Radiology 1988;169;59-63), in which the marking is incorporated on the MR image by using a special imaging sequence. More specifically, when a predetermined plane alone is selectively applied with 90° pulse before the imaging and then the normal imaging is carried out, the signal from the predetermined plane disappears and this portion appears as a black line (tag) on the obtained MR image. This line (tag) can be provided at any desired constant intervals in parallel, and the lattice shaped marking is also possible by making the tagging in the perpendicular direction instantaneously. It has also become possible recently to make the tagging in any desired 3D shape (C.J. Hardy, et al., J. Magnetic Resonance 1989;82;647-654). The tag can last for about one second, so that by taking the image within a prescribed time after the tagging, the movement during this period can be recognized from the flow of the tag. For example, in a case the mesh shaped tagging is made as shown in Fig. 16A at a time t0, if the object 36 is moving within the surrounding tissue 37, after an elapse of time t, the distortion on the mesh shaped tag as shown in Fig. 16B can be caused such that the movement of the object can be comprehended two dimensionally. Furthermore, by dividing the moving distance of the tag by the time t, it also becomes possible to obtain the moving speed of the object quantitatively. In this third embodiment, as shown in Fig. 17, the tag 38 in a point like shape is employed in order to make it easier to detect the position of the tag 38 in the MR image. Here, the detection of the position of the tag 38 can be achieved by detecting the lowest signal strength point within the MR image. Then, after an elapse of time such as 0.8 second during which the tag 38 does not disappear, the system controller 9 carries out another imaging. At this point, if the treatment target (tumor) 8 has moved, a displacement between the tag 38 and the focal point 7 is caused. This displacement is detected by the system controller 9 which subsequently controls the ultrasound applicator to shift the focal point 7 to the position of the tag 38, and then the tagging is made there again. Hereafter, the similar operation is repeated during the treatment of the first treatment position. After the treatment of the first treatment position is finished, at the timing of the expiration end, according to the treatment plan, the tagging is made at a next treatment position. Then, the same operation as in the case of the first treatment position is repeated. In a case the displacement between the tag 38 and the focal point 7 becomes greater than a prescribed value, the abrupt body movement of the patient or the malfunction of the apparatus may have occurred, so that the system controller 9 stops the ultrasound irradiation, and notifies the operator by means of the warning display or the alarm sound. It is to be noted that the chest belt 35 used in this third embodiment for detecting the respiration waveform can be replaced by the other respiration waveform detection means such as the impedance respiration monitor. Also, instead of the motion due to the respiration, this third embodiment can also be applied to the treatment of the heart muscle or the surrounding of the heart, by using the electrocardiogram similarly. It is also to be noted that the shape of the tag 38 may not necessarily be the point shaped one used above, and the tagging can be made at an intersection of three planes instead, or around the contour of the treatment target tumor in order to assist the operator's comprehension. Next, the fourth embodiment of a medical treatment apparatus according to the present invention will be described in detail. Here, those elements which are equivalent to the corresponding elements in the first embodiment of Fig. 1 will be given the same reference numerals as in the figure and their descriptions will be omitted. In this fourth embodiment, as shown in Fig. 18, the system controller is divided into a control circuit 9A and a sequence controller 9B, and there is provided a memory 28A connected with the control circuit 9A for storing the 3D data D0, D1, etc. of the interior of the patient, a memory 28B connected with the sequence controller 9B for storing the sequence data S1, S2, etc., and a light pen 29 provided in conjunction with the CRT 10. This fourth embodiment realizes the automatic focal point pursuit function as follows. First, in order to depict the tumor at high resolution and contrast, the sequence data S1 for T2 weighted imaging stored in the memory 28B are used to carry out the T2 weighted imaging sequence according to which the sequence controller 9B controls the gradient field power source 13 and the transmitter and receiver circuit 14. Then, the obtained image data are stored as the 3D data D0 in the memory 28A and while being displayed on the CRT 10. Then, the sequence data S2 for body temperature distribution measurement stored in the memory 28B is used to carry out the 3D temperature distribution data D1 before the ultrasound irradiation, to be stored in the memory 28A. Next, the control circuit 9A controls the driving circuits 12 at low output to warm up the patient's body below 45 °C for short period of time at the level of not influencing the living body, to obtain the 3D data D2 to be stored in the memory 28A. Then, the difference between the data D2 and D1 is taken and superposed onto the display of the data D0, so as to indicate a location at which the temperature has been increased, i.e., the focal point position, on the 3D image of the data D0. (Focal point positioning mode) As a result, the focal point can be set on the tumor accurately and the safe treatment can be carried out. By utilizing the fact that the current ultrasound irradiation point can be determined by measuring the temperature increase point in this manner, the temperature increasing point can be known in real time such that the intense ultrasound focal point can be made to follow the treatment portion automatically. More specifically, the focal point pursuit function is realized according to the sequence shown in Figs. 19A and 19B. First, Fig. 19A shows a sequence for the short pulse irradiation scheme, in which after the focal point is focused onto the patient according to the focal point positioning mode, the bursty irradiation of the intense ultrasound is started. when one short pulse irradiation is finished and immediately before the next short pulse irradiation starts, the temperature increase distribution data D3 is obtained and stored in the memory 28A. Then, from this data D3, the coordinate of the maximum temperature increase point is calculated. Here, it is also possible to set the center of gravity position of the temperature increase distribution as the focal point coordinate. Next, this coordinate (indicating the position of the first short pulse application) obtained from the data D3 is subtracted from the first coordinate of the focal point position obtained from the data D2 to calculate the displacement. Then, the control circuit 9A calculates the driving phase of the driving circuits 12 for driving the ultrasound transducer 2, and supplies the phase data to the phase control circuits 11. In response, the driving circuit 12 drives the ultrasound transducer 2 according to the phase data supplied from the phase control circuits 11. In a similar manner, the temperature increase distribution data D4, D5, etc. are obtained and according to these data, the ultrasound focal point is controlled to be always located at the maximum temperature increase position, such that the focal point can be maintained to be on the treatment portion which is moving because of the respiration motion. As a result, it becomes possible to prevent the failure to obtain the sufficient temperature increase due to the dislocation of the focal point, or the damaging of the not intended portion unintentionally. In this fourth embodiment, instead of the positioning of the focal point position during the short pulse irradiations, it is also possible to realize the focal point pursuit function during the continuous irradiation as shown Fig. 19B. In this case, the temperature increase distribution data D2, D3, etc. are obtained at prescribed time intervals, and the maximum point of the temperature increase can be measured from these data, such that the focal point is controlled to be always located at the maximum point calculated from these data. It is to be noted that in the scheme described above, the focal point moving control is carried out discretely, but it becomes possible to carry out the focal point moving control continuously by interpolating between the adjacent data such as D3 and D4 according to the foregoing data such as D2 and D3. It is also possible to realize the focal point pursuit function by predicting and interpolating the focal point moving route to the next point according to three foregoing data. It is also possible to use the temperature increase distribution measurement of this fourth embodiment in conjunction with the display of the image data, to realize even more accurate treatment. Also, the NMR parameters utilized for the measurement of the temperature distribution may be replaced by the sonic speed change on the ultrasound image, the temperature change of the tissue CT value on the X-ray CT image, etc. On the CRT 10, as shown in Fig. 20, the image data and the temperature increase data are displayed together, along with the temperature change of the maximum temperature increase point. Then, when the peak temperature increase reaches to 70 °C for example, the intense ultrasound irradiation is stopped and shifted to the next irradiation point. It is also possible to calculate the temperature increase distribution by the simulation instead of using the actually measured temperature distribution, which can be displayed along the actual image data.

Claims: A medical treatment apparatus, comprising: an imaging device (23) for obtaining image data of a treatment portion containing a treatment target (8); an energy irradiation means (2) for applying an energy irradiation onto the treatment target (8); and control means (9) for controlling the imaging device (23) and the energy irradiation means (2), such that the imaging device is controlled to obtain hot spot detection image data (66) after the energy irradiation means (2) is controlled to apply an energy irradiation at a prescribed level (65), characterized in that the control means (9) is adapted to detect (68) a hot spot on the basis of a temperature change in the treatment target caused by the energy irradiation at the prescribed level from the hot spot detection image data, and to control the energy irradiation means (2) to apply (72) a treatment energy irradiation at a treatment level higher than the prescribed level according to the detected hot spot. The apparatus of claim 1, wherein the control means (9) obtains the hot spot by comparing the hot spot detection image data with reference image data obtained by the imaging device (23) before the energy irradiation at the prescribed level. The apparatus of claim 1, wherein the control means (9) obtains the hot spot by extracting a portion in the hot spot detection image data exceeding a prescribed threshold for the change due to the temperature change. The apparatus of any one of claims 1 to 3, wherein the prescribed level at which the energy irradiation means (2) is controlled to apply the energy irradiation is a level for not damaging the treatment target (8). The apparatus of claim 4, wherein the prescribed level at which the energy irradiation means is controlled to apply the energy irradiation is a level for which a survival rate defined by the following equation (1) is greater than a prescribed value: where T o is a temperature before the energy irradiation, ΔT(t) is a time profile of a temperature change, Ea is an empirical activation energy, A is a proportional constant, R is a gas constant, and S is the survival rate. An medical treatment apparatus according to any one of claims 1 to 5, wherein the energy irradiation means is an ultrasound irradiation means (2) for applying an ultrasound irradiation focused to a treatment target (8), to raise a temperature of the treatment target (8); a temperature measurement means (32) is provided for measuring the temperature of the treatment target (8) after the ultrasound irradiation is applied by the ultrasound irradiation means (2); and an image of a treatment portion containing the treatment target (8) is obtained by said imaging device only when the temperature of the treatment target measured by the temperature measurement means (32) indicates a normal temperature of the treatment target that is substantially equal to a temperature of the treatment target before the ultrasound irradiation is applied. A medical treatment apparatus according to any one of claims 1 to 5, wherein the energy irradiation means is a ultrasound irradiation means (2) for applying an ultrasound irradiation to a treatment target (8), to increase a temperature of the treatment target and cause a degeneration at the treatment target; and comprising processing means for separating a change of the image due to the degeneration from a change of the image due to a temperature increase by subtracting a predicted change due to the temperature increase alone from the image obtaining by the imaging device (23). An ultrasound medical treatment apparatus, comprising: ultrasound irradiation means (2) for applying (65, 72) an ultrasound irradiation focused to a focal point (7) set on a treatment target (8); and temperature distribution measurement means for measuring temperature distribution of a treatment portion containing the treatment target (8) to obtain temperature increase point data; and control means (9) for controlling the temperature distribution measurement means and the ultrasound irradiation means (2), such that the temperature distribution measurement means is controlled to obtain the temperature increase point data after the ultrasound irradiation means (2) is controlled to apply (65) an ultrasound irradiation at a prescribed level; characterized in that the control means (9) is adapted to detect a temperature increase point from the temperature increase point data and to control the ultrasound irradiation means to apply (72) a treatment energy irradiation at a treatment level higher than the prescribed level after shifting (71) the focal point according to a displacement of the temperature increase point with respect to the focal point in the temperature distribution data obtained by the temperature distribution measurement means.

Inventors: AIDA SATOSHI, FUJIMOTO KATSUHIKO, ISHIBASHI YOSHIHARU, IZUMI MAMORU, OKAMOTO KAZUYA, SAITOH SHIROH, SHIBATA MARIKO, SUZUKI TAKUJI, AIDA, SATOSHI, FUJIMOTO, KATSUHIKO, ISHIBASHI, YOSHIHARU, IZUMI, MAMORU, OKAMOTO, KAZUYA, SAITOH, SHIROH, SHIBATA, MARIKO, SUZUKI, TAKUJI
Applicants: TOSHIBA KK, KABUSHIKI KAISHA TOSHIBA
Application year: 1994
Main classification: A61F7
IPC codes: G01R33, A61B19, A61N7, A61B17, A61B5, A61B8